EP1466632A1 - Implantable pouch seeded with insulin-producing cells to treat diabetes - Google Patents

Implantable pouch seeded with insulin-producing cells to treat diabetes Download PDF

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Publication number
EP1466632A1
EP1466632A1 EP04252017A EP04252017A EP1466632A1 EP 1466632 A1 EP1466632 A1 EP 1466632A1 EP 04252017 A EP04252017 A EP 04252017A EP 04252017 A EP04252017 A EP 04252017A EP 1466632 A1 EP1466632 A1 EP 1466632A1
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EP
European Patent Office
Prior art keywords
pouch
cells
polymer
lumen
glycolide
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EP04252017A
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German (de)
English (en)
French (fr)
Inventor
Alireza Rezania
Mark Zimmerman
Ragae M. Ghabrial
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LifeScan Inc
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LifeScan Inc
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/56—Porous materials, e.g. foams or sponges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • A61L27/18—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/38—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/38—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells
    • A61L27/3804—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells characterised by specific cells or progenitors thereof, e.g. fibroblasts, connective tissue cells, kidney cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P3/00—Drugs for disorders of the metabolism
    • A61P3/08—Drugs for disorders of the metabolism for glucose homeostasis
    • A61P3/10—Drugs for disorders of the metabolism for glucose homeostasis for hyperglycaemia, e.g. antidiabetics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P5/00—Drugs for disorders of the endocrine system
    • A61P5/48—Drugs for disorders of the endocrine system of the pancreatic hormones

Definitions

  • the present invention relates to an implantable pouch seeded with insulin releasing cells to treat diabetes. More specifically, the present invention provides an implantable porous pouch containing an opening for loading insulin releasing cells to treat diabetes mellitus and which opening may thereafter be closed and, if desired, sealed shut.
  • Pancreatic tissue consists of three parts: exocrine, endocrine, and ducts.
  • the endocrine pancreas contains islet cells responsible for release of four distinct hormones, and such islets consist of four separate cell types: ⁇ , ⁇ , ⁇ , and polypeptide cells that produce the hormones glucagons, insulin, somatostatin, and pancreatic polypeptide, respectively.
  • ⁇ , ⁇ , ⁇ , and polypeptide cells that produce the hormones glucagons, insulin, somatostatin, and pancreatic polypeptide, respectively.
  • Type I DM beta cells
  • Type II DM insensitivity of muscle or adipose tissues to the hormone insulin
  • Current methods of treatment of both Type I and Type II DM includes diet and exercise, oral hypoglycemic agents, insulin injections, insulin pump therapy, and whole pancreas or islet transplantation.
  • the most common treatment involves daily injections of an endogenous source of insulin such as porcine, bovine, or human insulin.
  • an endogenous source of insulin such as porcine, bovine, or human insulin.
  • the patient will usually follow a regime involving self-monitoring of blood glucose levels where insulin will be injected according to a prescribed plan based on the results of such blood analysis.
  • An alternative approach to immunoisolation is the creation of an immunologically privileged site by transplanting Sertoli cells into a nontesticular site in a mammal (US 5,849,285, US 6,149,907, US 5,958,404). This site allows for subsequent transplantation of islets that produce insulin.
  • the immune privileged site would allow transplantation of either human or animal derived islets.
  • One of the drawbacks of this approach is that the transplanted Sertoli and islet cells are not physically restricted to site of transplantation. This can lead to migration of these cells to unwanted tissue sites. If the islets migrate away from the Sertoli cells, it could ultimately lead to the loss of islets through loss of the immunosuppressive effect of the Sertoli cells as the immune-privileged environment created by Sertoli cells is most effective when the islets are in Close proximity.
  • tissue engineering offers alternative approaches to treat diabetes.
  • Tissue engineering strategies have explored the use of various biomaterials in combination with cells and/or growth factors to develop biological substitutes that ultimately can restore or improve tissue function.
  • scaffold materials have been extensively studied as tissue templates, conduits, barriers, and reservoirs useful for tissue repair.
  • synthetic and natural materials in the form of foams, sponges, gels, hydrogels, textiles, and nonwovens have been used in vitro and in vivo to reconstruct and/or regenerate biological tissue, as well as deliver chemotactic agents for inducing tissue growth (US5770417, US6022743, US5567612, US5759830).
  • scaffolds have been constructed as a substrate material upon which cells, such as islets, are seeded.
  • Traditional porous matrices such as polygycolic acid nonwovens or polylactic acid foams, though, have a pore size that is either too large or too small to sufficiently retain pancreatic islets or islet-like structures.
  • the biodegradable construct of the present invention provides such a three-dimensional Dorous matrix.
  • the present invention is directed to an implantable pouch that is suitable for use in seeding and subsequent implantation of plurality of mammalian cells including insulin-producing cells.
  • the walls of the pouch are biocompatible and composed of a foam matrix reinforced with a biocompatible mesh.
  • the lumen of the pouch is loaded with an insulin-secreting cell suspension.
  • the biocompatible matrix encapsulating the mesh is preferably porous, polymeric foam, preferably formed using a lyophilization process.
  • the construct may also be used to provide a vascular bed prior to introduction of insulin secreting cells.
  • the lumen of the pouch may be filled with a biocompatible plug, to restrict tissue growth into the lumen, and implanted into a clinically relevant site followed by removal of the plug at a later time and injection of the insulin-secreting cells into the lumen of the pouch.
  • the pouch may be optionally loaded with one or more biologically active compounds or hydrogels.
  • the wall of the pouch preferably is made from a polymer whose glass transition temperature is below physiologic temperature so that the pouch will minimize irritation when implanted in soft tissues.
  • the construct of the present invention can also act as a'vehicle to deliver cell-secreted biological factors or synthetic pharmaceuticals.
  • Such agents may direct up-regulation or down-regulation of growth factors, proteins, cytokines or proliferation of other cell types.
  • a number of cells may be seeded on such a pouch before or after implantation into a diseased mammal.
  • the implantable tissue scaffold pouch 1 consists of a wall 2 surrounding an interior lumen 5.
  • the wall 2 is preferably composed of a porous foam matrix 3 reinforced with, most preferably, a mesh 4.
  • the interior lumen will have a volume of at least 1 x 10 -3 cm 3 . Preferably it will be at least 0.1 cm 3 .
  • the number and size of the insulin-producing cells along with site of implantation will dictate the dimensions of the pouch 1.
  • the porous pouch 1 will generally have a longitudinal axis and a cross-section that may be circular, oval or polygonal. Preferred for ease of manufacture is an oval shaped cross-section.
  • Figure 1 depicts a pouch constructed from two rectangular sheets sealed on three sides and open at one end. As evident, though, from Figure 1, all that is necessary is a lumen to be formed by the wall 2 such that a cavity is formed sufficient for placement of islets or islet-like cells. Thus, the pouch could be constructed from one sheet or from multiple sheets and sealed in some appropriate manner together.
  • the walls 2 of the pouch 1 contain pores 6 that may range from about 0.1 to about 500 microns and preferably in the range of from about 5 to about 400 microns.
  • the lumen 5 of implantable pouch 1 may be filled with a hydrogel or a matrix containing a cell suspension or with a non-porous slab of nondegradable material that may be removed at a later time following transplantation and replaced with a cell suspension.
  • the foam component 3 of the wall 2 is preferably elastomeric, with pore size in the range of 5-400 ⁇ m.
  • the foam 3 may be loaded with biologically active or pharmaceutically active compounds (e.g. cytokines (e.g. interlukins 1-18; interferons ⁇ , ⁇ , and ⁇ ; growth factors; colony stimulating factors, chemokines, etc.), non-cytokine leukocyte chemotactic agents (e.g. C5a, LTB 4 , etc.), attachment factors, genes, peptides, proteins, nucleotides, anti-inflammatory agents, anti-apoptotic agents, carbohydrates or synthetic molecules.
  • biologically active or pharmaceutically active compounds e.g. cytokines (e.g. interlukins 1-18; interferons ⁇ , ⁇ , and ⁇ ; growth factors; colony stimulating factors, chemokines, etc.), non-cytokine leukocyte chemotactic agents (e.g. C5a, LTB 4
  • the reinforcing component 4 of the wall 2 can be comprised of any absorbable or non-absorbable biocompatible material, including textiles with woven, knitted, warped knitted (i.e., lace-like), non-woven, and braided structures.
  • the reinforcing component 4 has a mesh-like structure.
  • the fibers used to make the reinforcing component 4 can be monofilaments, yarns, threads, braids, or bundles of fibers. These fibers can be made of any biocompatible material including bioabsorbable materials such as polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), polydioxanone (PDO), trimethylene carbonate (TMC), polyvinyl alcohol (PVA), copolymers or blends thereof.
  • PLA polylactic acid
  • PGA polyglycolic acid
  • PCL polycaprolactone
  • PDO polydioxanone
  • TMC trimethylene carbonate
  • PVA polyvinyl alcohol copolymers or blends thereof.
  • the fibers are formed of a polyglycolic acid and polylactic acid copolymer at a 95:5 mole ratio. In another embodiment, the fibers are formed from a 100% PDO polymer.
  • the wall 2 of the implantable pouch 1 will be made with a biocompatible material that may be absorbable or non-absorbable.
  • the wall 2 will preferably be made from biocompatible materials that are flexible and thereby minimizing irritation to the patient.
  • the wall 2 will be made from polymers or polymer blends having glass transition temperature below physiologic temperature.
  • the pouch can be made with a polymer blended with a plasticizer that makes it flexible.
  • Nonabsorbable materials include, but are not limited to, polyamides, polyesters (e.g. polyethylene terephthalate, polybutyl terphthalate, copolymers and blends thereof), fluoropolymers (e.g. polytetrafluoroethylene and polyvinylidene fluoride, copolymers and blends thereof), polyolefins, polyvinyl resins (e.g. polystyrene, polyvinylpyrrolidone, etc.) and blends thereof.
  • polyamides e.g. polyethylene terephthalate, polybutyl terphthalate, copolymers and blends thereof
  • fluoropolymers e.g. polytetrafluoroethylene and polyvinylidene fluoride, copolymers and blends thereof
  • polyolefins e.g. polyvinyl resins (e.g. polystyrene, polyvinylpyrrolidone, etc.) and blend
  • bioabsorbable polymers can be used to make the wall 2 of the present invention.
  • suitable biocompatible and bioabsorbable polymers include but are not limited to polymers selected from the group consisting of aliphatic polyesters, poly(amino acids), copoly(ether-esters), polyalkylenes oxalates, polyamides, tyrosine derived polycarbonates, poly(iminocarbonates), polyorthoesters, polyoxaesters, polyamidoesters, polyoxaesters containing amine groups, poly(anhydrides), polyphosphazenes, biomolecules (i.e., biopolymers such as collagen, elastin, bioabsorbable starches, etc.) and blends thereof.
  • biocompatible absorbable polymers selected from the group consisting of aliphatic polyesters, copolymers and blends which include but are not limited to homopolymers and copolymers of lactide (which includes D-, L-, lactic acid and D-, L- and meso lactide), glycolide (including glycolic acid), oxaesters, epsilon-caprolactone, p-dioxanone, alkyl substituted derivatives of p-dioxanone (i.e.
  • the reinforcing component 4 of the wall 2 is preferably composed from lactide and glycolide sometimes referred to herein as simply homopolymers and copolymers of lactide and glycolide and copolymers of glycolide and epsilon-caprolactone, most preferred for use as a mesh is a copolymer that is from about 80 weight percent to about 100 weight percent glycolide with the remainder being lactide. More preferred are copolymers of from about 85 to about 95 weight percent glycolide with the remainder being lactide. Another preferred polymer is 100% PDO.
  • Preferred foam component 3 is composed of homopolymers, copolymers, or blends of glycolide, lactide, polydioxanone, and epsilon-caproloactone. More preferred are copolymers of glycolide and caprolactone. Most preferred is a 65:35 glycolide:caprolactone copolymer.
  • glycol is understood to include polyglycolic acid.
  • lactide is understood to include L-lactide, D-lactide, blends thereof, and lactic acid polymers and copolymers.
  • a particularly desirable composition includes an elastomeric copolymer of from about 35 to about 45 weight percent epsilon-caprolactone and from about 55 to about 65 weight percent glycolide, lactide (or lactic acid) and mixtures thereof.
  • Another particularly desirable composition includes para-dioxanone homopolymer or copolymers containing from about 0 to about 80 weight percent para-dioxanone and from about 0 to about 20 weight percent of either lactide, glycolide and combinations thereof.
  • the degradation time for the membrane in-vivo is preferably longer than 1 month but is shorter than 6 months and more preferably is longer than 1 month but less than 4 months.
  • the molecular weight of the polymers used in the present invention can be varied as is well know in the art to provide the desired performance characteristics. However, it is preferred to have aliphatic polyesters having a molecular weight that provides an inherent viscosity between about 0.5 to about 5.0 deciliters per gram (dl/g) as measured in a 0.1 g/dl solution of hexafluoroisopropanol at 25 °C, and preferably between about 0.7 and 3.5 deciliters per gram (dl/g).
  • the reinforcing component 4 of the wall 2 can be a nonwoven scaffold.
  • the nonwoven scaffold can be fabricated using wet-lay or dry-lay fabrication techniques. Fusing the fibers of the nonwoven scaffold of the tissue scaffold pouch 1 with another biodegradable polymer, using a thermal process, can further enhance the structural integrity of the fibrous nonwoven scaffold of the tissue scaffold pouch 1.
  • bioabsorbable thermoplastic polymer or copolymer such as polycaprolactone (PCL) in powder form, may be added to the nonwoven scaffold followed by a mild heat treatment that melts the PCL particles while not affecting the structure of the fibers.
  • This powder possesses a low melting temperature and acts as a binding agent later in the process to increase the tensile strength and shear strength of the nonwoven scaffold.
  • the preferred particulate powder size of PCL is in the range of 10-500 ⁇ m in diameter, and more preferably 10-150 ⁇ m in diameter.
  • Additional binding agents include a biodegradable polymeric binders selected from the group consisting of polylactic acid, polydioxanone and polyglycolic acid or combinations thereof.
  • the fibers in the nonwoven scaffold may be fused together by spraying or dip coating the nonwoven scaffold in a solution of another biodegradable polymer.
  • the foam 3 surrounding the lumen 5 of the present pouch 1 may be formed by a variety of techniques well known to those having ordinary skill in the art.
  • the polymeric starting materials may be foamed by lyophilization, supercritical solvent foaming, gas injection extrusion, gas injection molding or casting with an extractable material (e.g., salts, sugar or similar suitable materials).
  • the foam portion 3 of the pouch 1 may be made by a polymer-solvent phase separation technique, such as lyophilization.
  • a polymer solution can be separated into two phases by any one of the four techniques: (a) thermally induced gelation/crystallization; (b) non-solvent induced separation of solvent and polymer phases; (c) chemically induced phase separation, and (d) thermally induced spinodal decomposition.
  • the polymer solution is separated in a controlled manner into either two distinct phases or two bicontinuous phases. Subsequent removal of the solvent phase usually leaves a porous structure of density less than the bulk polymer and pores in the micrometer ranges.
  • the steps involved in the preparation of the foam component 3 of the wall 2 include choosing the appropriate solvents for the polymers to be lyophilized and preparing a homogeneous solution of the polymer in the solution.
  • the polymer solution then is subjected to a freezing and a vacuum drying cycle.
  • the freezing step phase-separates the polymer solution and the vacuum drying step removes the solvent by sublimation and/or drying, thus leaving a porous polymer structure, or an interconnected open-cell porous foam.
  • Suitable solvents that may be used in the preparation of the foam scaffold component 3 include, but are not limited to, tetrahydrofuran (THF), dimethylene fluoride (DMF), and polydioxanone (PDO), p-xylene, N-methyl pyrrolidone, dimethylformamide, chloroform, 1,2-dichloromethane, dimethylsulfoxide and mixtures thereof.
  • a preferred solvent is 1,4-dioxane.
  • a homogeneous solution of the polymer in the solvent is prepared using standard techniques.
  • the applicable polymer concentration or amount of solvent that may be utilized will vary with each system.
  • the amount of polymer in the solution can vary from about 0.01% to about 90% by weight and, preferably, will vary from about 0.05% to about 30% by weight, depending on factors such as the solubility of the polymer in a given solvent and the final properties desired in the foam scaffolding.
  • a mesh reinforcing material 4 When a mesh reinforcing material 4 will be used, it will be positioned between two thin (e.g., 0.4 mm) shims; it should be positioned in a substantially flat orientation at a desired depth in the mold.
  • a metal or Teflon insert that has a cross sectional area corresponding to that required for the pouch 1 is placed between two stretched layers of mesh.
  • the polymer solution is poured in a way that allows air bubbles to escape from between the layers of the mesh component.
  • the mold is tilted at a desired angle and pouring is effected at a controlled rate to best prevent bubble formation.
  • the mold is tilted at a desired angle and pouring is effected at a controlled rate to best prevent bubble formation.
  • the mold is tilted at an angle of greater than about 1 degree to avoid, bubble formation.
  • the rate of pouring should be slow enough to enable any air bubbles to escape from the mold, rather than to be trapped in the mold.
  • a mesh material is used as the reinforcing component 4, the density of the mesh openings is an important factor in the formation of a resulting tissue implant with the desired mechanical properties.
  • a low density, or open knitted mesh material is preferred.
  • One particularly preferred material is a 90/10 copolymer of PGA/PLA, sold under the tradename VICRYL (Ethicon, Inc., Somerville, NJ).
  • VICRYL VICRYL
  • Knitted VICRYL VKM-M available from Ethicon, Inc., Somerville, NJ.
  • Other knitted or woven mesh material that may be used in the pouch are 95/5 copolymer of PLA/PGA, sold under the tradename PANACRYL (Ethicon, Inc., Somerville, NJ), or 100% PDO polymer.
  • the mammalian cells loaded into the lumen 5 of the pouch 1 may be isolated from pancreatic tissue including the exocrine, endocrine, and ductal components of the pancreas. Alternatively, minced pancreatic tissue or ductal fragments may be loaded into the lumen 5 of the pouch 1. Furthermore, the cells may be cultured under standard culture conditions to expand the number of cells followed by removal of the cells from culture plates and administering into the device prior to implantation. Alternatively, the isolated cells may be injected directly into the pouch 1 and then cultured under conditions which promote proliferation and deposition of the appropriate biological matrix prior to in vivo implantation. In the preferred embodiment, the isolated cells are injected directly into the pouch 1 with no further in vitro culturing prior to in vivo implantation. In another embodiment, the cells are seeded into another porous biocompatible matrix, such as a nonwoven mat, a hydrogel, or combination thereof, followed by placement into the lumen 5 of the pouch.
  • another porous biocompatible matrix such as a nonwoven mat, a
  • Cells that can be seeded or cultured on the construct of the current invention include, but are not limited to cells expressing at least one characteristic marker of a pancreatic beta cell.
  • the cells can be seeded into the lumen 5 of the pouch of the present invention for a short period of time ( ⁇ 1 day) just prior to implantation, or cultured for longer (> 1 day) period to allow for cell proliferation and matrix synthesis within the pouch 1 prior to implantation.
  • the cell-seeded scaffold pouch 1 may be placed in a clinically convenient site such as the subcutaneous space, the mesentery, or the omentum.
  • the pouch 1 of the present invention will act as a vehicle to entrap the administered cells in place after in vivo transplantation into an ectopic site.
  • the failures can be circumvented by administering xenogeneic or allogeneic insulin-producing cells in combination with allogeneic or xenogeneic Sertoli cells which may aid in the survival of the islets and prevention of an immune response to the transplanted islets.
  • Xenogeneic, allogeneic, or transformed Sertoli cells can protect themselves in the kidney capsule while immunoprotecting allogeneic or xenogeneic islets.
  • the wall 2 of the pouch 1 may be modified either through physical or chemical means to contain biological or synthetic factors that promote attachment, proliferation, differentiation, and matrix synthesis of targeted cell types.
  • the bioactive factors may also comprise part of the matrix for controlled release of the factor to elicit a desired biological function.
  • Another embodiment would include delivery of small molecules that affect the up or down regulation of endogenous growth factors.
  • Growth factors, extracellular matrix proteins, and biologically relevant peptide fragments that can be used with the matrices of the current invention include, but are not limited to, members of TGF- ⁇ family, including TGF- ⁇ 1, 2, and 3, bone morphogenic proteins (BMP-2, -4, 6, -12, -13 and -14), fibroblast growth factors-1 and -2, platelet-derived growth factor-AA, and -BB, platelet rich plasma, insulin growth factor (IGF-I, II) growth differentiation factor (GDF-5, -6, -8, -10), angiogen, erythropoiethin, placenta growth factor, angiogenic factors such as vascular endothelial cell-derived growth factor (VEGF), cathelicidins, defensins, glucacgon-like peptide I, exendin-4, pleiotrophin, endothelin, parathyroid hormone, stem cell factor, colony stimulating factor, tenascin-C, tropoelastin, thro
  • a solution of the polymer to be lyophilized into a pouch was prepared.
  • the polymer used to manufacture the foam component was a copolymer of 35% PCL and 65% PGA (35/65 PCL/PGA) produced by Birmingham Polymers Inc. (Birmingham, AL) with an I.V. of 1.79 dL/g, as measured in HFIP at 30 °C.
  • a 95/5 weight ratio of 1,4-dioxane/(35/65 PCL/PGA) was weighed out.
  • the polymer and solvent were placed into a flask, which in turn was put into a water bath and stirred at 70°C for 5 hrs.
  • the solution was filtered using an extraction thimble (extra coarse porosity, type ASTM 170-220 (EC)) and stored in a flask.
  • extraction thimble extra coarse porosity, type ASTM 170-220 (EC)
  • Reinforcing mesh material formed of a 90/10 copolymer of polyglycolic/polylactic acid (PGA/PLA) knitted (Code VKM-M) mesh sold under the tradename VICRYL were rendered flat by ironing, using a compression molder at 80 °C/2 min. After preparing the meshes, 0.4-mm shims were placed at each end of a 15.3 ⁇ 15.3 cm aluminum mold, and two meshes were sized to fabricate the desired pouch size. The two mesh layers were stretched on top of each other between frame A and B as indicated in Figure 3 and the complex was then positioned on the shims allowing the meshes to be suspended in solution to be added.
  • PGA/PLA polyglycolic/polylactic acid
  • a metal or a Teflon insert that has a cross sectional area corresponding to that of the opening of the required pouch (0.4x8.0 or 0.4x4.0 mm 2 ) is placed between two stretched layers of mesh.
  • the polymer solution heated to 50°C is poured slowly from the side until the top mesh layer is completely covered. Approximately 60 ml of the polymer solution was slowly transferred into the mold, ensuring that the solution was well dispersed in the mold. The mold was then placed on a shelf in a Virtis, Freeze Mobile G freeze dryer.
  • freeze dry sequence used in this example was: 1) -17°C for 60 minutes; 2) -5°C for 60 minutes under vacuum 100 mT; 3) 5°C for 60 minutes under, vacuum 20 mT; 4) 20°C for 60 minutes under vacuum 20 mT.
  • Figure 1 shows the resulting pouch containing the reinforced foam 3 surrounding the lumen of the pouch following the removal of the insert.
  • Figure 2 depicts scanning electron micrograph (SEMs) of the cross-section of the pouch. The SEM clearly shows the lyophilized reinforced foam scaffold inside the pouch.
  • the mold assembly was then removed from the freezer and placed in a nitrogen box overnight. Following the completion of this process the resulting construct was carefully peeled out of the mold in the form of a foam/mesh sheet containing a removable insert.
  • the insert may be removed prior to loading of cells and in vivo implantation or removed at a later time following transplantation. In the latter case, cells are loaded into the lumen of the pouch upon removal of the insert.
  • a biodegradable pouch was fabricated following the process of Example 1, except a woven Vicryl (Code VWM-M), reinforcing mesh material formed of a 90/10 copolymer of polyglycolic/polylactic acid (PGA/PLA) was used.
  • a biodegradable pouch was fabricated following the process of Example 1, except a knitted reinforcing mesh material formed of 100% PDS was used.
  • This example illustrates seeding of murine islets within the lumen of the pouch described in this invention.
  • Murine Islets were isolated from Balb/c mice by collagenase digestion of the pancreas and Ficoll density gradient centrifugation followed by hand picking of islets.
  • Pouches were prepared as described in Example 1 and seeded with 500 fresh islets and cultured for 1 week in Hams-F10 (Gibco Life Technologies, Rockville, MD) supplemented with bovine serum albumin (0.5%), nicotinamide (10 mM), D-glucose (10 mM), L-glutamine (2 mM), IBMX (3-Isobutyl-1-methylxanthine, 50 mM), and penicillin/Streptomycin. Following 1 week, the islets residing in the pouches were stained with calcein and ethidium homodimer (Molecular Probes, Oregon) to assay for viability of the seeded cells. Majority of the islets stained positive for calcein indicating viable cells within the lumen of the pouch.

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  • Emergency Medicine (AREA)
  • Urology & Nephrology (AREA)
  • Hematology (AREA)
  • Materials For Medical Uses (AREA)
  • Prostheses (AREA)
  • Medicines Containing Material From Animals Or Micro-Organisms (AREA)
  • Medicinal Preparation (AREA)
EP04252017A 2003-04-02 2004-04-02 Implantable pouch seeded with insulin-producing cells to treat diabetes Withdrawn EP1466632A1 (en)

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US10/405,594 US20040197374A1 (en) 2003-04-02 2003-04-02 Implantable pouch seeded with insulin-producing cells to treat diabetes
US405594 2003-04-02

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EP (1) EP1466632A1 (zh)
JP (1) JP2004307505A (zh)
CN (1) CN100404074C (zh)
AU (1) AU2004201398A1 (zh)
CA (1) CA2462999A1 (zh)
TW (1) TW200501924A (zh)

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WO2006130851A2 (en) 2005-06-02 2006-12-07 Arizona Board Of Regents On Behalf Of The University Of Arizona Prevascularized devices and related methods
EP1743663A2 (en) * 2005-06-29 2007-01-17 Lifescan, Inc. Multi-compartment delivery system
DE102005042707A1 (de) * 2005-09-01 2007-03-08 Polymedics Innovations Gmbh Formkörper zur medizinischen Behandlung von Wunden

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CA2531022C (en) * 2003-07-03 2014-09-09 Jannette Dufour Compositions containing sertoli cells and myoid cells and use thereof in cellular transplants
US20080199507A1 (en) * 2005-06-17 2008-08-21 Rimon Therapeutics Ltd. Therapeutic Polymeric Pouch
EP2129339B1 (en) * 2007-03-29 2015-03-04 Tyrx, Inc. Biodegradable, polymer coverings for breast implants
EP3290061B1 (en) * 2009-08-28 2020-06-10 Sernova Corporation Methods and devices for cellular transplantation
US8518440B2 (en) * 2010-12-21 2013-08-27 Confluent Surgical, Inc. Biodegradable osmotic pump implant for drug delivery
FR3014316B1 (fr) * 2013-12-10 2017-01-20 Defymed Organe bioartificiel
US11857670B2 (en) * 2014-06-06 2024-01-02 Nanovault Medical, Llc Implantable cellular and biotherapeutic agent delivery canister
US11857673B2 (en) 2014-06-06 2024-01-02 Nanovault Medical, Llc Implantable cellular and biotherapeutic agent delivery canister
US11857672B2 (en) 2014-06-06 2024-01-02 Nanovault Medical, Llc Implantable cellular and biotherapeutic agent delivery canister
EP3273949A4 (en) * 2015-03-23 2018-12-12 The Regents of The University of California Thin film cell encapsulation devices
AU2017366791B2 (en) * 2016-11-03 2021-01-21 Arizona Board Of Regents On Behalf Of The University Of Arizona Methods, systems, and implantable devices for enhancing blood glucose regulation
CA3042866A1 (en) 2016-11-03 2018-05-11 Klearchos K. Papas Encapsulation device systems with oxygen sensors with or without exogenous oxygen delivery
SG10202104564SA (en) 2016-11-03 2021-06-29 Univ Arizona Methods and systems for real-time assessment of cells in encapsulation devices pre-and post-transplantation
CN110121311B (zh) 2016-11-03 2023-01-06 代表亚利桑那大学的亚利桑那董事会 有或无氧气输送的堆叠组织包封装置的系统
WO2019004379A1 (ja) 2017-06-29 2019-01-03 富士フイルム株式会社 移植用チャンバーおよび移植用デバイス

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EP1887870A2 (en) * 2005-06-02 2008-02-20 Arizona Board of Regents, on behalf of the University of Arizona Prevascularized devices and related methods
EP1887870A4 (en) * 2005-06-02 2012-02-22 Univ Arizona State PREVASCULARIZED DEVICES AND ASSOCIATED METHODS
EP1743663A2 (en) * 2005-06-29 2007-01-17 Lifescan, Inc. Multi-compartment delivery system
EP1743663A3 (en) * 2005-06-29 2007-09-19 Lifescan, Inc. Multi-compartment delivery system
DE102005042707A1 (de) * 2005-09-01 2007-03-08 Polymedics Innovations Gmbh Formkörper zur medizinischen Behandlung von Wunden

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CA2462999A1 (en) 2004-10-02
AU2004201398A1 (en) 2004-10-21
JP2004307505A (ja) 2004-11-04
CN1569236A (zh) 2005-01-26
CN100404074C (zh) 2008-07-23
US20040197374A1 (en) 2004-10-07
TW200501924A (en) 2005-01-16

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